EP3830594B1 - Diffusionsgewichtete niederfeld-magnetresonanztomografie - Google Patents

Diffusionsgewichtete niederfeld-magnetresonanztomografie Download PDF

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EP3830594B1
EP3830594B1 EP19752818.5A EP19752818A EP3830594B1 EP 3830594 B1 EP3830594 B1 EP 3830594B1 EP 19752818 A EP19752818 A EP 19752818A EP 3830594 B1 EP3830594 B1 EP 3830594B1
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field
low
images
echo
period
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EP3830594A1 (de
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Rafael O'halloran
Laura Sacolick
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Hyperfine Inc
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Hyperfine Inc
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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
    • G01R33/381—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using electromagnets
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/445—MR involving a non-standard magnetic field B0, e.g. of low magnitude as in the earth's magnetic field or in nanoTesla spectroscopy, comprising a polarizing magnetic field for pre-polarisation, B0 with a temporal variation of its magnitude or direction such as field cycling of B0 or rotation of the direction of B0, or spatially inhomogeneous B0 like in fringe-field MR or in stray-field imaging
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/563—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution of moving material, e.g. flow contrast angiography
    • G01R33/56341—Diffusion imaging
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
    • G01R33/389—Field stabilisation, e.g. by field measurements and control means or indirectly by current stabilisation
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/561—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution by reduction of the scanning time, i.e. fast acquiring systems, e.g. using echo-planar pulse sequences
    • G01R33/5615—Echo train techniques involving acquiring plural, differently encoded, echo signals after one RF excitation, e.g. using gradient refocusing in echo planar imaging [EPI], RF refocusing in rapid acquisition with relaxation enhancement [RARE] or using both RF and gradient refocusing in gradient and spin echo imaging [GRASE]
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/561—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution by reduction of the scanning time, i.e. fast acquiring systems, e.g. using echo-planar pulse sequences
    • G01R33/5613—Generating steady state signals, e.g. low flip angle sequences [FLASH]

Definitions

  • Magnetic resonance imaging provides an important imaging modality for numerous applications and is widely utilized in clinical and research settings to produce images of the inside of the human body.
  • MRI is based on detecting magnetic resonance (MR) signals, which are electromagnetic waves emitted by atoms in response to state changes resulting from applied electromagnetic fields.
  • MR magnetic resonance
  • NMR nuclear magnetic resonance
  • Detected MR signals may be processed to produce images, which in the context of medical applications, allows for the investigation of internal structures and/or biological processes within the body for diagnostic, therapeutic and/or research purposes.
  • MRI provides an attractive imaging modality for biological imaging due to the ability to produce non-invasive images having relatively high resolution and contrast without the safety concerns of other modalities (e.g., without needing to expose the subject to ionizing radiation, e.g., x-rays, or introducing radioactive material to the body). Additionally, MRI is particularly well suited to provide soft tissue contrast, which can be exploited to image subject matter that other imaging modalities are incapable of satisfactorily imaging. Moreover, MR techniques are capable of capturing information about structures and/or biological processes that other modalities are incapable of acquiring. However, there are a number of drawbacks to MRI that, for a given imaging application, may involve the relatively high cost of the equipment, limited availability and/or difficulty in gaining access to clinical MRI scanners and/or the length of the image acquisition process.
  • the trend in clinical MRI has been to increase the field strength of MRI scanners to improve one or more of scan time, image resolution, and image contrast, which, in turn, continues to drive up costs.
  • the vast majority of installed MRI scanners operate at 1.5 or 3 tesla (T), which refers to the field strength of the main magnetic field B 0 .
  • T tesla
  • a rough cost estimate for a clinical MRI scanner is approximately one million dollars per tesla, which does not factor in the substantial operation, service, and maintenance costs involved in operating such MRI scanners.
  • conventional high-field MRI systems typically require large superconducting magnets and associated electronics to generate a strong uniform static magnetic field (B 0 ) in which an object (e.g., a patient) is imaged.
  • B 0 uniform static magnetic field
  • the size and expense of MRI systems generally limits their usage to facilities, such as hospitals and academic research centers, which have sufficient space and resources to purchase and maintain them.
  • the high cost and substantial space requirements of high-field MRI systems results in limited availability of MRI scanners. As such, there are frequently clinical situations in which an MRI scan would be beneficial, but due to one or more of the limitations discussed above, is not practical or is impossible, as discussed in further detail below.
  • a diffusion-prepared turbo spin echo readout (DP-TSE) sequence was developed and compared with the conventional diffusion-weighted single-shot echo-planar-imaging sequence on a 0.35 T MRI-guided radiotherapy system (ViewRay).
  • a diffusion technique with excellent geometric fidelity, accurate, and reproducible ADC measurement was demonstrated for longitudinal tumor response assessment using a low-field MRI-guided radiotherapy system.
  • a first aspect of the present invention is provided by a low-field magnetic resonance imaging (MRI) system in accordance with claim 1.
  • MRI magnetic resonance imaging
  • a second aspect of the present invention is provided by a computer-implemented method of operating a low-field magnetic resonance imaging (MRI) system in accordance with claim 10.
  • MRI magnetic resonance imaging
  • a third aspect of the present invention is provided by a non-transitory computer-readable medium in accordance with claim 13.
  • the MRI scanner market is overwhelmingly dominated by high-field systems, and particularly for medical or clinical MRI applications.
  • the general trend in medical imaging has been to produce MRI scanners with increasingly greater field strengths, with the vast majority of clinical MRI scanners operating at 1.5T or 3T, with higher field strengths of 7T and 9T used in research settings.
  • high-field refers generally to MRI systems presently in use in a clinical setting and, more particularly, to MRI systems operating with a main magnetic field (i.e., a B 0 field) at or above 1.5T, though clinical systems operating between .5T and 1.5T are often also characterized as "high-field.”
  • Field strengths between approximately .2T and .5T have been characterized as “mid-field” and, as field strengths in the high-field regime have continued to increase, field strengths in the range between .5T and 1T have also been characterized as mid-field.
  • low-field refers generally to MRI systems operating with a B 0 field of less than or equal to approximately 0.2T, though systems having a B 0 field of between .2T and approximately .3T have sometimes been characterized as low-field as a consequence of increased field strengths at the high end of the high-field regime.
  • low-field MRI systems operating with a B 0 field of less than .1T are referred to herein as "very low-field” and low-field MRI systems operating with a B 0 field of less than 10mT are referred to herein as "ultra-low field.”
  • high-field MRI systems require specially adapted facilities to accommodate the size, weight, power consumption and shielding requirements of these systems.
  • a 1.5T MRI system typically weighs between 4-10 tons and a 3T MRI system typically weighs between 8-20 tons.
  • high-field MRI systems generally require significant amounts of heavy and expensive shielding. Many mid-field scanners are even heavier, weighing between 10-20 tons due, in part, to the use of very large permanent magnets and/or yokes.
  • MRI systems typically consume large amounts of power.
  • common 1.5T and 3T MRI systems typically consume between 20-40kW of power during operation
  • available .5T and .2T MRI systems commonly consume between 5-20kW, each using dedicated and specialized power sources.
  • power consumption is referenced as average power consumed over an interval of interest.
  • the 20-40kW referred to above indicates the average power consumed by conventional MRI systems during the course of image acquisition, which may include relatively short periods of peak power consumption that significantly exceeds the average power consumption (e.g., when the gradient coils and/or RF coils are pulsed over relatively short periods of the pulse sequence).
  • Intervals of peak (or large) power consumption are typically addressed via power storage elements (e.g., capacitors) of the MRI system itself.
  • the average power consumption is the more relevant number as it generally determines the type of power connection needed to operate the device.
  • available clinical MRI systems must have dedicated power sources, typically requiring a dedicated three-phase connection to the grid to power the components of the MRI system. Additional electronics are then needed to convert the three-phase power into single-phase power utilized by the MRI system.
  • the many physical requirements of deploying conventional clinical MRI systems creates a significant problem of availability and severely restricts the clinical applications for which MRI can be utilized.
  • the low SNR of MR signals produced in the low-field regime has prevented the development of a relatively low cost, low power and/or portable MRI system.
  • Conventional "low-field" MRI systems operate at the high end of what is typically characterized as the low-field range (e.g., clinically available low-field systems have a floor of approximately .2T) to achieve useful images.
  • conventional low-field MRI systems share many of the same drawbacks.
  • conventional low-field MRI systems are large, fixed and immobile installments, consume substantial power (requiring dedicated three-phase power hook-ups) and require specially shielded rooms and large dedicated spaces.
  • the challenges of low-field MRI have prevented the development of relatively low cost, low power and/or portable MRI systems that can produce useful images.
  • the inventors have developed techniques enabling portable, low-field, low power and/or lower-cost MRI systems that can improve the wide-scale deployability of MRI technology in a variety of environments beyond the current MRI installments at hospitals and research facilities.
  • MRI can be deployed in emergency rooms, small clinics, doctor's offices, in mobile units, in the field, etc. and may be brought to the patient (e.g., bedside) to perform a wide variety of imaging procedures and protocols.
  • Some embodiments include very low-field MRI systems (e.g., .1T, 50mT, 20mT, etc.) that facilitate portable, low-cost, low-power MRI, significantly increasing the availability of MRI in a clinical setting.
  • clinical MRI system refers to an MRI system that produces clinically useful images, which refers to images having sufficient resolution and adequate acquisition times to be useful to a physician or clinician for its intended purpose given a particular imaging application. As such, the resolutions/acquisition times of clinically useful images will depend on the purpose for which the images are being obtained.
  • the numerous challenges in obtaining clinically useful images in the low-field regime is the relatively low SNR. Specifically, the relationship between SNR and B 0 field strength is approximately B 0 5/4 at field strength above .2T and approximately B 0 3/2 at field strengths below .1T.
  • the SNR drops substantially with decreases in field strength with even more significant drops in SNR experienced at very low field strength.
  • This substantial drop in SNR resulting from reducing the field strength is a significant factor that has prevented development of clinical MRI systems in the very low-field regime.
  • the challenge of the low SNR at very low field strengths has prevented the development of a clinical MRI system operating in the very low-field regime.
  • clinical MRI systems that seek to operate at lower field strengths have conventionally achieved field strengths of approximately the .2T range and above. These MRI systems are still large, heavy and costly, generally requiring fixed dedicated spaces (or shielded tents) and dedicated power sources.
  • an MRI system can be transported to the patient to provide a wide variety of diagnostic, surgical, monitoring and/or therapeutic procedures, generally, whenever and wherever needed.
  • FIG. 1 is a block diagram of typical components of a MRI system 100.
  • MRI system 100 comprises computing device 104, controller 106, pulse sequences store 108, power management system 110, and magnetics components 120.
  • system 100 is illustrative and that a MRI system may have one or more other components of any suitable type in addition to or instead of the components illustrated in FIG. 1 .
  • a MRI system will generally include these high level components, though the implementation of these components for a particular MRI system may differ vastly, as discussed in further detail below.
  • magnetics components 120 comprise B 0 magnet 122, shim coils 124, RF transmit and receive coils 126, and gradient coils 128.
  • Magnet 122 may be used to generate the main magnetic field B 0 .
  • Magnet 122 may be any suitable type or combination of magnetics components that can generate a desired main magnetic B 0 field.
  • the B 0 magnet is typically formed using superconducting material generally provided in a solenoid geometry, requiring cryogenic cooling systems to keep the B 0 magnet in a superconducting state.
  • high-field B 0 magnets are expensive, complicated and consume large amounts of power (e.g., cryogenic cooling systems require significant power to maintain the extremely low temperatures needed to keep the B 0 magnet in a superconducting state), require large dedicated spaces, and specialized, dedicated power connections (e.g., a dedicated three-phase power connection to the power grid).
  • Conventional low-field B 0 magnets e.g., B 0 magnets operating at .2T
  • B 0 magnets are implemented using permanent magnets, which to produce the field strengths to which conventional low-field systems are limited (e.g., between .2T and .3T due to the inability to acquire useful images at lower field strengths), need to be very large magnets weighing 5-20 tons.
  • the B 0 magnet of conventional MRI systems alone prevents both portability and affordability.
  • Gradient coils 128 may be arranged to provide gradient fields and, for example, may be arranged to generate gradients in the B 0 field in three substantially orthogonal directions (X, Y, Z).
  • Gradient coils 128 may be configured to encode emitted MR signals by systematically varying the B 0 field (the B 0 field generated by magnet 122 and/or shim coils 124) to encode the spatial location of received MR signals as a function of frequency or phase.
  • gradient coils 128 may be configured to vary frequency or phase as a linear function of spatial location along a particular direction, although more complex spatial encoding profiles may also be provided by using nonlinear gradient coils.
  • a first gradient coil may be configured to selectively vary the B 0 field in a first (X) direction to perform frequency encoding in that direction
  • a second gradient coil may be configured to selectively vary the B 0 field in a second (Y) direction substantially orthogonal to the first direction to perform phase encoding
  • a third gradient coil may be configured to selectively vary the B 0 field in a third (Z) direction substantially orthogonal to the first and second directions to enable slice selection for volumetric imaging applications.
  • conventional gradient coils also consume significant power, typically operated by large, expensive gradient power sources, as discussed in further detail below.
  • MRI is performed by exciting and detecting emitted MR signals using transmit and receive coils, respectively (often referred to as radio frequency (RF) coils).
  • Transmit/receive coils may include separate coils for transmitting and receiving, multiple coils for transmitting and/or receiving, or the same coils for transmitting and receiving.
  • a transmit/receive component may include one or more coils for transmitting, one or more coils for receiving and/or one or more coils for transmitting and receiving.
  • Transmit/receive coils are also often referred to as Tx/Rx or Tx/Rx coils to generically refer to the various configurations for the transmit and receive magnetics component of an MRI system. These terms are used interchangeably herein.
  • RF transmit and receive coils 126 comprise one or more transmit coils that may be used to generate RF pulses to induce an oscillating magnetic field B 1 .
  • the transmit coil(s) may be configured to generate any suitable types of RF pulses.
  • Power management system 110 includes electronics to provide operating power to one or more components of the low-field MRI system 100.
  • power management system 110 may include one or more power supplies, gradient power components, transmit coil components, and/or any other suitable power electronics needed to provide suitable operating power to energize and operate components of MRI system 100.
  • power management system 110 comprises power supply 112, power component(s) 114, transmit/receive switch 116, and thermal management components 118 (e.g., cryogenic cooling equipment for superconducting magnets).
  • Power supply 112 includes electronics to provide operating power to magnetic components 120 of the MRI system 100.
  • power supply 112 may include electronics to provide operating power to one or more B 0 coils (e.g., B 0 magnet 122) to produce the main magnetic field for the low-field MRI system.
  • Transmit/receive switch 116 may be used to select whether RF transmit coils or RF receive coils are being operated.
  • Power component(s) 114 may include one or more RF receive (Rx) preamplifiers that amplify MR signals detected by one or more RF receive coils (e.g., coils 126), one or more RF transmit (Tx) power components configured to provide power to one or more RF transmit coils (e.g., coils 126), one or more gradient power components configured to provide power to one or more gradient coils (e.g., gradient coils 128), and one or more shim power components configured to provide power to one or more shim coils (e.g., shim coils 124).
  • Rx RF receive
  • Tx RF transmit
  • the power components are large, expensive and consume significant power.
  • the power electronics occupy a room separate from the MRI scanner itself.
  • the power electronics not only require substantial space, but are expensive complex devices that consume substantial power and require wall mounted racks to be supported.
  • the power electronics of conventional MRI systems also prevent portability and affordable of MRI.
  • MRI system 100 includes controller 106 (also referred to as a console) having control electronics to send instructions to and receive information from power management system 110.
  • Controller 106 may be configured to implement one or more pulse sequences, which are used to determine the instructions sent to power management system 110 to operate the magnetic components 120 in a desired sequence (e.g., parameters for operating the RF transmit and receive coils 126, parameters for operating gradient coils 128, etc.).
  • controller 106 also interacts with computing device 104 programmed to process received MR data.
  • computing device 104 may process received MR data to generate one or more MR images using any suitable image reconstruction process(es).
  • Controller 106 may provide information about one or more pulse sequences to computing device 104 for the processing of data by the computing device. For example, controller 106 may provide information about one or more pulse sequences to computing device 104 and the computing device may perform an image reconstruction process based, at least in part, on the provided information.
  • computing device 104 typically includes one or more high performance work-stations configured to perform computationally expensive processing on MR data relatively rapidly. Such computing devices are relatively expensive equipment on their own.
  • MRI systems including high-field, mid-field and low-field systems
  • high-field, mid-field and low-field systems are large, expensive, fixed installations requiring substantial dedicated and specially designed spaces, as well as dedicated power connections.
  • the inventors have developed low-field, including very-low field, MRI systems that are lower cost, lower power and/or portable, significantly increasing the availability and applicability of MRI.
  • a portable MRI system is provided, allowing an MRI system to be brought to the patient and utilized at locations where it is needed.
  • some embodiments include an MRI system that is portable, allowing the MRI device to be moved to locations in which it is needed (e.g., emergency and operating rooms, primary care offices, neonatal intensive care units, specialty departments, emergency and mobile transport vehicles and in the field).
  • locations in which it is needed e.g., emergency and operating rooms, primary care offices, neonatal intensive care units, specialty departments, emergency and mobile transport vehicles and in the field.
  • challenges face the development of a portable MRI system, including size, weight, power consumption and the ability to operate in relatively uncontrolled electromagnetic noise environments (e.g., outside a specially shielded room).
  • An aspect of portability involves the capability of operating the MRI system in a wide variety of locations and environments.
  • currently available clinical MRI scanners are required to be located in specially shielded rooms to allow for correct operation of the device and is one (among many) of the reasons contributing to the cost, lack of availability and non-portability of currently available clinical MRI scanners.
  • the MRI system must be capable of operation in a variety of noise environments.
  • the inventors have developed noise suppression techniques that allow the MRI system to be operated outside of specially shielded rooms, facilitating both portable/transportable MRI as well as fixed MRI installments that do not require specially shielded rooms.
  • noise suppression techniques allow for operation outside specially shielded rooms
  • these techniques can also be used to perform noise suppression in shielded environments, for example, less expensive, loosely or ad-hoc shielding environments, and can be therefore used in conjunction with an area that has been fitted with limited shielding, as the aspects are not limited in this respect.
  • a further aspect of portability involves the power consumption of the MRI system.
  • current clinical MRI systems consume large amounts of power (e.g., ranging from 20kW to 40kW average power consumption during operation), thus requiring dedicated power connections (e.g., dedicated three-phase power connections to the grid capable of delivering the required power).
  • dedicated power connections e.g., dedicated three-phase power connections to the grid capable of delivering the required power.
  • the requirement of a dedicated power connection is a further obstacle to operating an MRI system in a variety of locations other than expensive dedicated rooms specially fitted with the appropriate power connections.
  • the inventors have developed low power MRI systems capable of operating using mains electricity such as a standard wall outlet (e.g., 120V/20A connection in the U.S.) or common large appliance outlets (e.g., 220-240V/30A), allowing the device to be operated anywhere common power outlets are provided.
  • mains electricity such as a standard wall outlet (e.g., 120V/20A connection in the U.S.) or common large appliance outlets (e.g., 220-240V/30A), allowing the device to be operated anywhere common power outlets are provided.
  • a standard wall outlet e.g., 120V/20A connection in the U.S.
  • common large appliance outlets e.g., 220-240V/30A
  • Low-field MR has been explored in limited contexts for non-imaging research purposes and narrow and specific contrast-enhanced imaging applications, but is conventionally regarded as being unsuitable for producing clinically useful images.
  • the resolution, contrast, and/or image acquisition time is generally not regarded as being suitable for clinical purposes including, but not limited to, tissue differentiation, blood flow or perfusion imaging, diffusion-weighted (DW) or diffusion tensor (DT) imaging, functional MRI (fMRI), etc.
  • DW diffusion-weighted
  • DT diffusion tensor
  • fMRI functional MRI
  • DWI diffusion-weighted imaging
  • MRI magnetic resonance imaging
  • Performing DWI is technically challenging in that DWI is an inherently low-SNR sequence and places high demands on MRI hardware including the gradient coils and amplifiers.
  • Low-cost, low-field MR scanners amplify the technical challenges of implementing DWI.
  • One example of a low-cost, low-field MR scanner is described in U.S. Pat. App. Pub. No. 2018/0164390 , titled "Electromagnetic Shielding for Magnetic Resonance Imaging Methods and Apparatus,".
  • the inventors have developed a pulse sequence referred to herein as the diffusion-weighted steady state free precession (DW-SSFP) sequence, that is specifically designed for use and/or optimal performance in the low-field context.
  • DW-SSFP sequence has higher SNR efficiency and lower demands on gradient amplifiers than conventional DWI sequences.
  • the inventors have developed several innovations to enable a low-field MR scanner to perform the DW-SSFP sequence including, but not limited to, the ones described below.
  • FIG. 2 schematically illustrates a time-sequence of aspects of the DW-SSFP sequence in accordance with some embodiments.
  • FIG. 2 illustrates a radio-frequency (RF) time sequence indicating times when the RF coil is transmitting an RF pulse (e.g., RF pulse 210), a data acquisition (DAQ) time sequence indicating times when emitted magnetic resonance signals are being acquired by the MR receive coils, and a gradient time sequence indicating times when the x-,y-, and z- gradients are activated to provide spatial encoding of the emitted MR signals.
  • RF radio-frequency
  • DAQ data acquisition
  • the DW-SSFP sequence includes an RF pulse 210 immediately followed by a readout period 220 during which magnetic resonance data is acquired, as shown in FIG. 2 .
  • FIG. 3 illustrates a process 300 for using magnetic resonance data acquired during the readout period 220 immediately following the RF pulse 210 to correct image blurring due to B 0 field drift.
  • act 310 the phase of the free induction decay (FID) resulting from the RF pulse is captured during readout period 220.
  • the slope of the phase of the FID is directly proportional to the B 0 field strength.
  • Process 300 then proceeds to act 320, where the phase of the FID determined in act 310 is fit to a linear model to improve robustness to noise due to B 0 field drift.
  • Process 300 then proceeds to act 330, where the fit phase is used to remove the phase introduced into the acquired MR signals caused by B 0 field drift, thereby correcting the blurring in the resulting images.
  • Some low-field MR scanners include gradient components that produce lower gradient amplitudes than a conventional high-field MRI system.
  • diffusion weighted imaging requires a substantial amount of gradient encoding.
  • eddy current pre-emphasis which is used for image correction, requires extra room above the maximum gradient amplitude of any gradient encoding waveform to perform pre-emphasis.
  • embodiments of the DW-SSFP pulse sequence include a diffusion weighted encoding gradient waveform that is not trapezoidal.
  • An example of such a waveform is shown in FIG. 2 and includes a shaped attack edge 230. As shown, the shaped attack edge does not have a constant slope, but rather has a slope that decreases as the maximum value is approached.
  • the shaped attack edge ensures that the pre-emphasized resulting waveform has a flat top at the maximum.
  • the decay edge of diffusion-weighted encoding gradient waveform is unaffected, such that pre-emphasis can be used to reduce the resulting eddy currents during the imaging block (corresponding to the time periods 240 and 250 in FIG. 2 ).
  • the diffusion weighted encoding gradients occur over a relatively long timespan and as such, the available signal to be detected is reduced.
  • the readout time following diffusion-weighted gradient encoding also referred to herein as the "imaging block"
  • the inhomogeneity of the B 0 field in some low-field scanners may cause longer readouts to have blurring and image warping.
  • the DW-SSFP sequence extends the imaging block by encoding multiple echoes during time periods 240 and 250 in the imaging block.
  • a line of k-space is measured during a first time period 240, the gradient polarity is reversed, and the same line of k-space is measured again during a second time period 250.
  • Such a readout scheme reduces encoding time and increases SNR efficiency.
  • the gradients used in DWI sequences are typically large, resulting in residual eddy currents in the magnetic components of the low-field MRI system.
  • the residual eddy currents cause warping of the image along the slowest encoding direction. Warping also arises from the inhomogeneous B 0 field, as noted above.
  • the warping is in opposite directions for adjacent echoes in the pulse sequence (e.g., the echo encoded during time period 240 and the echo encoded during time period 250 have opposite gradient polarities). By comparing the adjacent echoes having opposite gradient polarities, the images can de-warped during image reconstruction and the images can be combined to increase SNR.
  • FIG. 4 illustrates a process 400 for increasing SNR for diffusion weighted imaging using a pulse sequence with multiple echoes having different polarities in accordance with some embodiments.
  • act 410 MR signals corresponding to a first gradient echo of the DW-SSFP pulse sequence (e.g., the echo encoded during time period 240) are acquired.
  • FIG. 5A shows images reconstructed based on the MR signals acquired during time period 240.
  • Process 400 then proceeds to act 420, where MR signals corresponding to a second gradient echo of the DW-SSFP pulse sequence (e.g., the echo encoded during time period 250) are acquired.
  • FIG. 5B shows images reconstructed based on the MR signals acquired during the time period 250.
  • Process 400 then proceeds to act 430 where the images acquired during time period 240 and the images acquired during time period 250 are de-warped during image reconstruction.
  • Process 400 then proceeds to act 440 where the de-warped images are combined.
  • FIG. 4C shows images obtained by de-warping the images from FIGS. 4A-B and combining the images to increase SNR in accordance with some embodiments.
  • One or more aspects and embodiments of the present disclosure involving the performance of processes or methods may utilize program instructions executable by a device (e.g., a computer, a processor, or other device) to perform, or control performance of, the processes or methods.
  • a device e.g., a computer, a processor, or other device
  • inventive concepts may be embodied as a computer readable storage medium (or multiple computer readable storage media) (e.g., a computer memory, one or more compact discs, optical discs, magnetic tapes, flash memories, circuit configurations in Field Programmable Gate Arrays or other semiconductor devices, or other tangible computer storage medium) encoded with one or more programs that, when executed on one or more computers or other processors, perform methods that implement one or more of the various embodiments described above.
  • the computer readable medium or media can be transportable, such that the program or programs stored thereon can be loaded onto one or more different computers or other processors to implement various ones of the aspects described above.
  • computer readable media may be non-transitory media.
  • program or “software” are used herein in a generic sense to refer to any type of computer code or set of computer-executable instructions that can be employed to program a computer or other processor to implement various aspects as described above. Additionally, it should be appreciated that according to one aspect, one or more computer programs that when executed perform methods of the present disclosure need not reside on a single computer or processor, but may be distributed in a modular fashion among a number of different computers or processors to implement various aspects of the present disclosure.
  • Computer-executable instructions may be in many forms, such as program modules, executed by one or more computers or other devices.
  • program modules include routines, programs, objects, components, data structures, etc. that perform particular tasks or implement particular abstract data types.
  • functionality of the program modules may be combined or distributed as desired in various embodiments.
  • data structures may be stored in computer-readable media in any suitable form.
  • data structures may be shown to have fields that are related through location in the data structure. Such relationships may likewise be achieved by assigning storage for the fields with locations in a computer-readable medium that convey relationship between the fields.
  • any suitable mechanism may be used to establish a relationship between information in fields of a data structure, including through the use of pointers, tags or other mechanisms that establish relationship between data elements.
  • the embodiments can be implemented in any of numerous ways.
  • the embodiments may be implemented using hardware, software or a combination thereof.
  • the software code can be executed on any suitable processor or collection of processors, whether provided in a single computer or distributed among multiple computers.
  • any component or collection of components that perform the functions described above can be generically considered as a controller that controls the above-discussed function.
  • a controller can be implemented in numerous ways, such as with dedicated hardware, or with general purpose hardware (e.g., one or more processor) that is programmed using microcode or software to perform the functions recited above, and may be implemented in a combination of ways when the controller corresponds to multiple components of a system.
  • a computer may be embodied in any of a number of forms, such as a rack-mounted computer, a desktop computer, a laptop computer, or a tablet computer, as non-limiting examples. Additionally, a computer may be embedded in a device not generally regarded as a computer but with suitable processing capabilities, including a Personal Digital Assistant (PDA), a smartphone or any other suitable portable or fixed electronic device.
  • PDA Personal Digital Assistant
  • a computer may have one or more input and output devices. These devices can be used, among other things, to present a user interface. Examples of output devices that can be used to provide a user interface include printers or display screens for visual presentation of output and speakers or other sound generating devices for audible presentation of output. Examples of input devices that can be used for a user interface include keyboards, and pointing devices, such as mice, touch pads, and digitizing tablets. As another example, a computer may receive input information through speech recognition or in other audible formats.
  • Such computers may be interconnected by one or more networks in any suitable form, including a local area network or a wide area network, such as an enterprise network, and intelligent network (IN) or the Internet.
  • networks may be based on any suitable technology and may operate according to any suitable protocol and may include wireless networks, wired networks or fiber optic networks.
  • some aspects may be embodied as one or more methods.
  • the acts performed as part of the method may be ordered in any suitable way. Accordingly, embodiments may be constructed in which acts are performed in an order different than illustrated, which may include performing some acts simultaneously, even though shown as sequential acts in illustrative embodiments.
  • a reference to "A and/or B", when used in conjunction with open-ended language such as “comprising” can refer, in one embodiment, to A only (optionally including elements other than B); in another embodiment, to B only (optionally including elements other than A); in yet another embodiment, to both A and B (optionally including other elements); etc.
  • the phrase "at least one,” in reference to a list of one or more elements, should be understood to mean at least one element selected from any one or more of the elements in the list of elements, but not necessarily including at least one of each and every element specifically listed within the list of elements and not excluding any combinations of elements in the list of elements.
  • This definition also allows that elements may optionally be present other than the elements specifically identified within the list of elements to which the phrase "at least one" refers, whether related or unrelated to those elements specifically identified.
  • At least one of A and B can refer, in one embodiment, to at least one, optionally including more than one, A, with no B present (and optionally including elements other than B); in another embodiment, to at least one, optionally including more than one, B, with no A present (and optionally including elements other than A); in yet another embodiment, to at least one, optionally including more than one, A, and at least one, optionally including more than one, B (and optionally including other elements); etc.

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Claims (13)

  1. Niederfeld-Magnetresonanztomografiesystem (100), MRT, das Folgendes umfasst: eine Vielzahl von Magnetkomponenten (120), einschließlich:
    eines B0-Magneten (122), der konfiguriert ist zum Erzeugen eines Niederfeld-Hauptmagnetfelds Bo;
    mindestens einer Gradientenspule (128), die konfiguriert ist, im Betrieb eine räumliche Kodierung der emittierten Magnetresonanzsignale bereitzustellen;
    mindestens einer Hochfrequenzkomponente (126), RF, die konfiguriert ist, im Betrieb die emittierten Magnetresonanzsignale zu erfassen; und
    mindestens eines Reglers (106), der konfiguriert ist zum Betreiben einer oder mehrerer der Vielzahl von Magnetkomponenten in Übereinstimmung mit mindestens einer Pulssequenz, die eine diffusionsgewichtete Gradientenkodierungsperiode gefolgt von mehreren Echoperioden (240, 250), während derer Magnetresonanzsignale erzeugt und erfasst werden, aufweist, wobei:
    mindestens zwei der mehreren Echoperioden jeweils kodierten Echos mit entgegengesetzter Gradientenpolarität entsprechen,
    wobei die mehreren Echoperioden eine erste Echoperiode (240) einschließen, während der ein erstes kodiertes Echo eine erste Gradientenpolarität aufweist sowie eine zweite Echoperiode (250), die unmittelbar auf die erste Echoperiode folgt, während der ein zweites kodiertes Echo eine zur ersten Gradientenpolarität entgegengesetzte zweite Gradientenpolarität aufweist,
    wobei die mindestens eine Pulssequenz weiter einen HF-Puls (210), gefolgt von einer Ausleseperiode (220), umfasst, wobei die Ausleseperiode zeitlich mit der diffusionsgewichteten Gradientenkodierungsperiode überlappt, und
    wobei die diffusionsgewichtete Gradientenkodierungsperiode einen diffusionsgewichteten Gradientenpuls mit asymmetrischen Anstiegs- und Abklingflanken einschließt, so dass der diffusionsgewichtete Gradientenpuls nicht trapezförmig ist, wobei die Anstiegsflanke (230) des diffusionsgewichteten Gradientenpulses eine variierende Steigung aufweist.
  2. Niederfeld-MRT-System nach Anspruch 1, wobei der mindestens eine Regler weiter konfiguriert ist zum Rekonstruieren mindestens eines Bildes, basierend, zumindest teilweise, auf den Magnetresonanzsignalen, die während jeder der mehreren Echoperioden erfasst wurden.
  3. Niederfeld-MRT-System nach Anspruch 2, wobei die Rekonstruktion des mindestens einen Bildes umfasst:
    Rekonstruieren einer ersten Vielzahl von Bildern, basierend, zumindest teilweise, auf den während der ersten Echoperiode erfassten Magnetresonanzsignalen;
    Rekonstruieren einer zweiten Vielzahl von Bildern, basierend, zumindest teilweise, auf den während der zweiten Echoperiode erfassten Magnetsignalen;
    Entzerren der ersten Vielzahl von Bildern und der zweiten Vielzahl von Bildern; und
    Kombinieren der entzerrten ersten Vielzahl von Bildern und der zweiten Vielzahl von Bildern, um das mindestens eine Bild zu rekonstruieren.
  4. Niederfeld-MRT-System nach Anspruch 2, wobei der mindestens eine Regler weiter konfiguriert ist zum:
    Bestimmen einer Phase des freien Induktionszerfalls während der Ausleseperiode;
    Anpassen der bestimmten Phase an ein lineares Modell; und
    Rekonstruieren des mindestens einen Bildes, basierend, zumindest teilweise, auf der Anpassungsphase, um die Bildunschärfe aufgrund des Drifts im Hauptmagnetfeld Bozu korrigieren.
  5. Niederfeld-MRT-System nach Anspruch 1, wobei der mindestens eine Regler weiter konfiguriert ist zum:
    Rekonstruieren einer ersten Vielzahl von Bildern, basierend, zumindest teilweise, auf den während der ersten Echoperiode erfassten Magnetresonanzsignalen;
    Rekonstruieren einer zweiten Vielzahl von Bildern, basierend, zumindest teilweise, auf den während der zweiten Echoperiode erfassten Magnetsignalen;
    Entzerren der ersten Vielzahl von Bildern und der zweiten Vielzahl von Bildern;
    Kombinieren der entzerrten ersten Vielzahl von Bildern und der zweiten Vielzahl von Bildern, um kombinierte Bilder zu erzeugen;
    Bestimmen einer Phase des freien Induktionszerfalls während der Ausleseperiode;
    Anpassen der bestimmten Phase an ein lineares Modell; und
    Rekonstruieren des mindestens einen Bildes, basierend, zumindest teilweise, auf der Anpassungsphase und den kombinierten Bildern.
  6. Niederfeld- MRT-System nach Anspruch 1, wobei der B0-Magnet konfiguriert ist zum Erzeugen eines B0-Felds mit einer Stärke von ungefähr 0,2 T oder weniger und ungefähr 0,1 T oder mehr.
  7. Niederfeld-MRT-System nach Anspruch 1, wobei der B0-Magnet konfiguriert ist zum Erzeugen eines B0-Felds mit einer Stärke von ungefähr 0,1 T oder weniger und ungefähr 50 mT oder mehr.
  8. Niederfeld-MRT-System nach Anspruch 1, wobei der B0-Magnet konfiguriert ist zum Erzeugen eines B0-Felds mit einer Stärke von ungefähr 50 mT oder weniger und von ungefähr 20 mT oder mehr.
  9. Niederfeld-MRT-System nach Anspruch 1, wobei der B0-Magnet konfiguriert ist zum Erzeugen eines B0-Felds mit einer Stärke von ungefähr 20 mT oder weniger und von ungefähr 10 mT oder mehr.
  10. Computerimplementiertes Verfahren zum Betreiben eines Niederfeld-Magnetresonanztomografiesystems (100), MRT, um eine diffusionsgewichtete Bildgebung durchzuführen, wobei das Niederfeld-MRT-System eine Vielzahl von Magnetkomponenten (120) einschließt, einschließlich eines Bo-Magneten (122) , der konfiguriert ist zum Erzeugen eines Niederfeld-Hauptmagnetfelds Bo, mindestens einer Gradientenspule (128), die konfiguriert ist, im Betrieb eine räumliche Kodierung der emittierten Magnetresonanzsignale bereitzustellen, und mindestens einer Hochfrequenzkomponente (126) , die konfiguriert ist, im Betrieb die emittierten Magnetresonanzsignale zu erfassen, wobei das Verfahren Folgendes umfasst:
    Regeln einer oder mehrerer der Vielzahl von Magnetkomponenten in Übereinstimmung mit mindestens einer Pulssequenz, aufweisend eine diffusionsgewichtete Gradientenkodierungsperiode gefolgt von mehreren Echoperioden (240, 250), während derer Magnetresonanzsignale erzeugt und erfasst werden, zu betreiben, wobei mindestens zwei der mehreren Echoperioden jeweils kodierten Echos mit entgegengesetzter Gradientenpolarität entsprechen, wobei:
    wobei die mehreren Echoperioden eine erste Echoperiode (240) einschließen, während der ein erstes kodiertes Echo eine erste Gradientenpolarität aufweist sowie eine zweite Echoperiode (250), die unmittelbar auf die erste Echoperiode folgt, während der ein zweites kodiertes Echo eine zur ersten Gradientenpolarität entgegengesetzte zweite Gradientenpolarität aufweist,
    wobei die mindestens eine Pulssequenz weiter einen HF-Puls (210), gefolgt von einer Ausleseperiode (220), umfasst, wobei die Ausleseperiode zeitlich mit der diffusionsgewichteten Gradientenkodierungsperiode überlappt, und
    wobei die diffusionsgewichtete Gradientenkodierungsperiode einen diffusionsgewichteten Gradientenpuls mit asymmetrischen Anstiegs- und Abklingflanken einschließt, so dass der diffusionsgewichtete Gradientenpuls nicht trapezförmig ist, wobei die Anstiegsflanke (230) des diffusionsgewichteten Gradientenpulses eine variierende Steigung aufweist.
  11. Computerimplementiertes Verfahren nach Anspruch 10, wobei das Verfahren weiter umfasst:
    Rekonstruieren einer ersten Vielzahl von Bildern, basierend, zumindest teilweise, auf den während der ersten Echoperiode erfassten Magnetresonanzsignalen;
    Rekonstruieren einer zweiten Vielzahl von Bildern, basierend, zumindest teilweise, auf den während der zweiten Echoperiode erfassten Magnetsignalen;
    Entzerren der ersten Vielzahl von Bildern und der zweiten Vielzahl von Bildern; und
    Kombinieren der entzerrten ersten Vielzahl von Bildern und der zweiten Vielzahl von Bildern, um das mindestens eine Bild zu rekonstruieren.
  12. Computerimplementiertes Verfahren nach Anspruch 10, wobei das Verfahren weiter umfasst:
    Bestimmen einer Phase des freien Induktionszerfalls während der Ausleseperiode;
    Anpassen der bestimmten Phase an ein lineares Modell; und
    Rekonstruieren des mindestens einen Bildes, basierend, zumindest teilweise, auf der Anpassungsphase, um die Bildunschärfe aufgrund des Drifts im Hauptmagnetfeld B0 zu korrigieren.
  13. Nicht-transitorisches computerlesbares Medium, das mit einer Vielzahl von Befehlen kodiert ist, die, wenn sie von mindestens einem Computerprozessor, der konfiguriert ist zum Regeln eines Niederfeld-Magnetresonanztomografiesystems, MRT, ausgeführt werden, den mindestens einen Computerprozessor veranlassen, ein Verfahren zum Betrieb des Niederfeld-MRT-Systems gemäß einem der Ansprüche 10 bis 12 durchzuführen.
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